Medical device coating methods and devices

ABSTRACT

Devices and methods for applying a polymeric coating to a medical device. The steps of the coating process including applying a liquid polymeric material to the surface of the medical device, then directing a stream of gas to impinge on the surface of the medical device. Excess liquid polymeric material is removed from the surface of the medical device. The devices used in the coating process and the coated medical device are also part of this invention.

FIELD OF THE INVENTION

The present invention relates generally to a medical device having asurface treatment applied over a portion of its surface. Moreparticularly, the present invention relates to implantable medicaldevices having drug release coatings including a therapeutic substancein a polymeric carrier.

BACKGROUND OF THE INVENTION

There are a number of medical conditions which may be effectivelytreated with implantable medical devices. In many cases, the therapeuticeffect of the implantable medical device may be enhanced, if the deviceincludes a drug release coating including a therapeutic substance in apolymeric carrier. Two examples of implantable medical devices which mayinclude such drug release coatings are endovascular stents and vascularfilters.

Intravascular diseases are commonly treated by relatively non-invasivetechniques such as percutaneous transluminal angioplasty (PTA) andpercutaneous transluminal coronary angioplasty (PTCA). These angioplastytechniques typically involve the use of a guidewire and a ballooncatheter. In these procedures, a balloon catheter is advanced over aguidewire such that the balloon is positioned proximate a restriction ina diseased vessel. The balloon is then inflated and the restriction inthe vessel is opened.

While angioplasty techniques have gained wide acceptance, abrupt closureand restenosis have been identified as possible subsequent occurrences.Abrupt closure refers to the acute occlusion of a vessel immediatelyafter or within the initial hours following a dilation procedure. Abruptclosure can result in myocardial infarction if blood flow is notrestored in a timely manner. The primary mechanisms of abrupt closuresare arterial dissection and/or thrombosis. Restenosis refers to there-narrowing of an artery after an initially successful angioplasty.Restenosis occurs primarily within the initial six months afterangioplasty, and is believed due to the proliferation and migration ofthe cellular components of the arterial wall.

Endovascular stents are placed in the dilated segment of a vessel lumento mechanically block the effects of abrupt closure and restenosis. Sucha stent is disclosed in U.S. Pat. No. 5,514,154 to Lau et al.

Recent developments have led to stents which can provideanti-thrombogenic and other medications to regions of a blood vesselwhich have been treated by angioplasty or other interventionaltechniques. In U.S. Pat. No. 5,464,650, Berg et al. disclose a methodfor making an intravascular stent by applying to the stent, and inparticular to its tissue-contacting surface, a solution which includes asolvent, a polymer dissolved in the solvent, and a therapeutic substancedispersed in the solvent. After the solution is applied to the stent,the solvent is evaporated leaving the polymer/therapeutic agent surfacetreatment. Berg et. al. assert that these devices are capable ofproviding both short term medication delivery, over the initial hoursand days after treatment, as well as long term medication delivery, overthe weeks and months after treatment.

The process disclosed by Berg et al., which uses a polymeric carrier, isprone to the formation of polymeric surface imperfections during thecoating process. This is especially evident on stents, which generallyinclude many wire like members with interstitial spaces therebetween.The surface imperfections can include strands of drug laden polymericmaterial hanging loosely from or extending across the interstitialspaces in the stent. The imperfections can also include chunks orthickened coating portions at particular points relative to the rest ofthe coating. These imperfections, because of their drug deliveringcapabilities, may cause adverse effects. Loose strands or strands acrossinterstitial spaces may not be secure, and thus, may enter the bloodstream and fail to provide local treatment. If these agents are releasedto locations other than the targeted area, unwanted side effects mayresult. An uneven coating may also result in non-uniform treatment ofthe vessel wall.

As mentioned previously, vascular filters are another type ofimplantable medical device which may benefit from the inclusion of adrug release coating including a therapeutic substance in a polymericcarrier. One of the most common applications for vascular filters is thetreatment of Deep Venous Thrombosis (DVT). Deep Venous Thrombosispatients experience clotting of blood in the large veins of the lowerportions of the body. These patients are constantly at risk of a clotbreaking free and traveling via the inferior vena cava to the heart andlungs. This process is known as pulmonary embolization. Pulmonaryembolization can frequently be fatal, because large blood clots caninterfere with the function of the heart and/or lungs. For example, alarge blood clot which becomes trapped proximate the heart may interferewith the life-sustaining pumping action of the heart. A blood clot whichpasses through the heart will be pumped into the lungs and may cause ablockage in the pulmonary arteries. A blockage of this type in the lungswill interfere with the oxygenation of the blood causing shock or death.

Pulmonary embolization may be successfully prevented by the appropriateplacement of a vascular filter in the vascular system of a patient'sbody. Placement of the filter may be accomplished by performing alaparotomy with the patient under general anesthesia. However,intravenous insertion is often the preferred method of placing avascular in a patient's vascular system.

In the treatment of Deep Venous Thrombosis, a vascular filter is placedin the inferior vena cava of a patient. The inferior vena cava is alarge vessel which returns blood to the heart from the lower part of thebody. The inferior vena cava may be accessed through the patient'sfemoral vein.

Vascular filters may be placed in other locations when treating otherconditions. For example, if blood clots are expected to approach theheart and lungs from the upper portion of the body, a vascular filtermay be positioned in the superior vena cava. The superior vena cava is alarge vessel which returns blood to the heart from the upper part of thebody. The superior vena cava may by accessed through the jugular vein,located in the patient's neck. Once placed inside a blood vessel, avascular filter acts to catch and hold blood clots. The flow of bloodaround the captured clots allows the body's lysing process to dissolvethe clots.

SUMMARY OF THE INVENTION

The present invention pertains to implantable medical devices havingdrug release coatings including a therapeutic substance in a polymercarrier. The present invention provides a method of applying a coatingto an implantable medical device which is evenly distributed over all ofthe surfaces of the device. Two examples of implantable medical deviceswhich may be coated using this process are stents and thrombosisfilters. This method of coating may also be used with other implantablemedical devices. Also, this coating method may be used with stents ofboth self-expanding and balloon expandable designs.

Stents are normally comprised of a skeletal frame which includesopenings and a lumen which extends longitudinally through the stent. Avariety of processes are known for fabricating stents. A stent mayconsist of a plurality of filaments or fibers which are wound or braidedtogether to form a continuous structure. Alternately, the skeletal frameof a stent may be formed by removing material from a tubular elementusing a laser cutting process. A stent may be comprised of anybiocompatible material possessing the structural and mechanicalattributes necessary for supporting a diseased vessel.

Often, it is beneficial to both stent and treat a localized area of adiseased vessel. A therapeutic agent, therefore, can be incorporatedinto a polymer and applied to the stent as a polymeric surfacetreatment. Incorporation of a therapeutic agent into a surface treatmentgreatly enhances the scope of this medical device by transforming thestent into a drug delivery system. Drugs and treatments which utilizeanti-thrombogenic agents, anti-angiogenisis agent, anti-proliferativeagents, growth factors and radio chemicals may be readily deployed fromwithin the matrix of the polymer surface treatment.

The application of such a surface treatment is generally accomplished byapplying a coating solution to the stent. Typically, this coatingsolution includes a solvent, a polymer dissolved in the solvent and atherapeutic substance dispersed in the solvent. The coating solution maybe applied to the stent using a variety of methods. For example, thesolution may be applied to the stent by immersing the stent in liquidcoating solution. Alternately, the coating solution may be applied tothe stent with a brush. Finally, in a preferred embodiment, the coatingsolution may be sprayed onto the stent.

Solvent selection is critical to a functioning surface treatment. It isessential that the solvent is capable of placing the polymer intosolution and that the solvent and polymer chosen do not materially alterthe therapeutic character of the therapeutic agent. On the other hand,the therapeutic agent needs only to be dispersed throughout the solvent.The therapeutic agent, therefore, may be either in a true solution withthe solvent or dispersed in fine particles within the solvent.

It is preferred that the polymeric coating be evenly distributed overthe stent. Although the procedures for applying a polymeric surfacetreatments are optimized, they still often leave polymeric fibers,polymeric particles, or other polymeric surface aberrations orimperfections on the stent. These aberrations or imperfections in thepolymeric coating may take on numerous sizes and shapes. Regardless ofthe application process utilized, several types of imperfections arecommon. Examples of these imperfections are polymeric fibers, which spanacross the openings of the skeletal framework of the stent, and lumpscreated by an overabundance of polymeric material in a localized area.Imperfections in the polymeric coating may be a result ofdisproportionate application of the coating solution, or the settling ofexcessive material in a particular location. At a minimum, theimperfections are unsightly. More importantly, imperfections may createadverse secondary effects.

The adverse secondary effects which may arise are correlated to the typeof polymeric imperfections. Polymeric fibers are prone to two adverseeffects; the fibers may dislodge from the stent, or they may releasetheir therapeutic agents into the blood stream. Because fibers spanacross openings in the skeletal framework of the stent, they areattached typically at few locations. Expansion of the stent may dislodgethese imperfections sending them into the circulatory system. At thispoint, there exists no control over the drug delivery capabilities ofthese rogue fibers. The release of drugs in undesired locations islikely to cause secondary effects. On the other hand, polymeric fibersmay remain attached to the stent. Some of the fibers which remainattached to the stent may not engage the wall of the blood vessel. Inthis instance, the entire surface of the polymeric fibers is free torelease therapeutic agent directly into the blood stream, causing othersecondary effects.

Polymeric lumps are caused by an overabundance of polymeric material ina localized area, these lumps may also cause secondary effects. Asmentioned above, the goal of applying a polymeric surface treatment to astent is to have uniform coverage and uniform release of a therapeuticsubstance. When there are areas of excess coverage on the stent, thetargeted diseased tissue may receive a non-uniform dosage of thereleased therapeutic agent. For therapeutic agents, especially oneswhich promote or restrict endothelial cell growth, uneven release maycause non-optimal treatment. Another problem created by polymeric lumpsis that the lumps may be in a location of the stent where they do notcontact the wall of the blood vessel. In this instance, the entiresurface area of the lumps will be free to release therapeutic agentdirectly into the blood stream, causing other secondary effects.

The present invention provides a method of applying an even coating toan implantable medical device either alone or in a combination with atherapeutic substance. The process begins with the step of preparing acoating solution preferably including a polymer, a solvent, and atherapeutic substance. The coating solution is then applied to the stentby dipping, spraying or any other acceptable method. A tool or assemblyas described herein is then used to direct a gas stream so that the gasstream impinges on the surfaces of the stent. When the gas from the gasstream strikes the surfaces of the stent, it displaces excess coatingsolution. The tool or assembly may be moved to direct the gas stream atthe stent from a plurality of different locations and from a pluralityof different angles. The tool or assembly may also be in continuousrotational motion such that the gas streams generally impinge across theentire circumference of the stent. The tool may be adapted so that itmay be passed through the entire lumen of the stent. The flow of gasthrough the openings and around the wires of the stent is sufficient todisplace excess coating solution, any lumps, fibers, etc. formed by thecoating solution and will be blown off the surfaces of the stent by thegas stream. Once the excess coating solution has been removed from thesurfaces of the stent, the solvent of the coating solution is allowed toevaporate, thereby leaving on the surface of the stent, a polymercoating. As described above, the polymer coating ideally includes atherapeutic agent. Because all imperfections were removed before thecoating solution was allowed to dry, the polymer coating which resultsfrom this process was evenly distributed across the surface of thestent.

It should be understood that the coating method described above may beused in conjunction with any stent design. For example, this coatingmethod may be used with both self-expanding and balloon expandablestents. The coating method described above may also be used withimplantable medical devices other than stents. For example, a thrombosisfilter may be coated using a coating method described above.

A typical thrombosis filter includes a body member and a plurality ofelongated struts. Each strut has a free end and a joined end. The joinedend of each strut is fixably attached to the body member. The strutsradiate outwardly from the body member such that the thrombus filter isgenerally conical in shape. When the thrombosis is deployed inside ablood vessel, the free ends of the struts engage the blood vessel wall.The body member of the thrombosis filter is held in a position proximatethe center of the blood vessel by the plurality of struts which engagethe blood vessel walls with opposing force vectors.

The walls of the blood vessel are lined with a thin inner membrane orintima. When the free ends of the thrombus filter disrupt this innermembrane, the body responds in a process known as neointimalhyperplasia, or endothelial growth. As a result of this process, thedisrupted area of the inner membrane is overgrown with a number of newcells. The free ends of the thrombosis filter struts are encapsulatedwith new cell growth within 2-3 weeks of the implant of the filter.

Due to endothelial growth, thrombus filters placed in the blood vesselof a patient become affixed in the blood vessel walls within 2-3 weeksafter being implanted. Because the free ends of the thrombus filterstruts contacting the blood vessel walls become fixed in this way, manythrombosis filters cannot be removed percutaneously after being in placefor more than two weeks. Applying a polymer coating including atherapeutic substance in a polymer carrier to the free ends of avascular filter struts may assist in preventing or reducing endothelialgrowth proximate the free ends of the struts.

When the thrombosis filter is disposed in a blood vessel, the conicalformation of struts acts to trap or capture blood clots. The generallyconical shape of the formation of struts serves to urge captured bloodclots toward the center of the blood flow. The flow of blood around thecaptured blood clots allows the body's natural lysing process todissolve the clots. Applying a polymer coating including a therapeuticsubstance in a polymeric carrier to the vascular filter may assist thebody in dissolving blood clots.

The present invention provides a method which may be used to apply anevenly distributed polymeric coating to an implantable medical devicesuch as a thrombus filter. The process begins with the step of preparinga coating solution preferably including a polymer, a solvent, and atherapeutic substance. The coating solution is then applied to selectedsurfaces of the thrombus filter. A tool or assembly is then used todirect gas streams so that they impinge on the surfaces of the thrombusfilter. When the gas of the gas streams strikes the surfaces of thethrombus filter, it displaces excess coating solution. To assure thatthe gas streams impinge upon substantially all of the surfaces of thethrombus filter, the tool may be rotated or moved in a linear direction.The tool or assembly may also be moved to a variety of positions. Theflow of gas around the struts and body member of the thrombus filter issufficient to displace excess coating solution. Once the excess coatingsolution has been removed from the surfaces of the thrombosis filter,the solvent in the coating solution is allowed to evaporate therebyleaving on the surface of the thrombosis filter a polymer coating whichpreferably includes a therapeutic agent. Because all imperfections wereremoved before the solvent was allowed to evaporate, the polymer coatingresulting from this process is evenly distributed across the surfaces ofthe thrombosis filter.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a stent in accordance with an exemplaryembodiment of the present invention;

FIG. 2 is a magnified, partial plan view of the stent of FIG. 1,illustrating the polymeric surface aberrations and imperfections arisingfrom a polymeric coating procedure;

FIG. 3 is a plan view of a stent and an assembly to direct a gas streamat the stent surface;

FIG. 4 is a magnified, partial plan view of the stent of FIG. 1,illustrating an evenly applied polymeric coating applied using thecoating and surface treating method of the present invention;

FIG. 5 is a plan view of a stent and an alternate assembly for directinga gas stream at the stent surface;

FIG. 6 is a plan view of a stent and another alternate assembly fordirecting a gas stream at the stent surface;

FIG. 7 is a plan view of a stent and a further alternate assembly fordirecting a gas stream at the stent surface; and

FIG. 8 is a perspective view of a thrombosis filter and an assembly fordirecting a gas stream at the filter surface.

DETAILED DESCRIPTION OF THE INVENTION

The following detailed description should be read with reference to thedrawings, in which like elements in different drawings are numberedidentically. The drawings which are not necessarily to scale, depictselected embodiments and are not intended to limit the scope of theinvention.

Examples of constructions, materials, dimensions, and manufacturingprocesses are provided for selected elements. All other elements employthat which is known to those of skill in the field of the invention.Those skilled in the art will recognize that many of the examplesprovided have suitable alternatives which may be utilized.

FIG. 1 is a perspective view of a stent 10 having a skeletal frame 15.Skeletal frame 15 of stent 10 includes wire-like members or struts 12forming a distinct, repetitive serpentine pattern. This repetitiveserpentine pattern includes multiple U-shaped curves 14. Skeletal frame15 also includes a plurality of openings or apertures 16. With norecognizable beginning or end to this serpentine pattern, each wire 12forms an expandable serpentine element 18. Serpentine elements 18 arearranged along the longitudinal axis of stent 10 so that abuttingserpentine elements 18 may be joined together with additional wires 12.Skeletal frame 15 substantially forms a lumen 20 extendinglongitudinally through stent 10.

The term "wire", as used in describing the material of skeletal frame 15should not be mistaken as being limited to metallic materials. In fact,the "wire" forming stent 10 may be comprised of any biocompatiblematerial possessing the structural and mechanical attributes necessaryfor supporting a diseased vessel. Thus, both metallic and non-metallicmaterials are suitable. Examples of preferred biocompatible metallicmaterials include stainless steel, tantalum, gold, titanium, andnickel-titanium alloy. Preferred non-metallic materials may be selectedfrom the following list, which is not exhaustive: poly(L-lactide)(PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA),poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide)(PLLA/PGA), poly(D, L-lactide-co-glycolide) (PLA/PGA),poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide(PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate(PHBT), poly(phosphazene), polyD,L-lactide-co-caprolactone) (PLA/PCL),poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN),poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxybutyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate),polyurethane, polysiloxane and their copolymers.

Skeletal frame 15 of stent 10 may be formed through various methods. Forexample, skeletal frame 15 may be assembled from a plurality of wires 12joined together by welding or soldering. Skeletal frame 15 may be moldedin one piece using an injection molding process. Skeletal frame 15 mayalso be comprised of a plurality of filaments or fibers which are woundor braided together to form a continuous structure. Finally, in apreferred embodiment, skeletal frame 15 may be formed by removingmaterial from a tubular element using a LASER cutting process.

Often it is beneficial to both stent and treat a localized area of adiseased vessel. A therapeutic agent, therefore, can be incorporatedinto a polymer and applied to stent 10 as a polymeric surface treatment.The incorporation of a therapeutic agent into a surface treatmentgreatly enhances the scope of this medical device by transforming thestent into a drug-delivery system. Drugs and treatments which utilizeanti-thrombogenic agents, anti-angiogenisis agents, anti-proliferativeagents, growth factors, and radiochemicals may be readily deployed fromwithin the matrix of the polymeric surface treatment. Specific examplesof preferred therapeutic agents include angiopeptin, colchicine,lovastatin, trapidil, ticlopidine, hirudin, Taxol, and heparin. Specificexamples of growth factors which may serve as therapeutic agents includeVEGF, TGF-beta, IGF, PDGF, and FGF.

The application of such a surface treatment is generally accomplished byapplying a coating solution to stent 10. Typically, this coatingsolution includes a solvent, a polymer dissolved in the solvent, and atherapeutic substance dispersed in the solvent. The coating solution maybe applied to stent 10 using a variety of methods. For example, thesolution may be applied to stent 10 by immersing stent 10 in the coatingsolution. Alternately, the coating solution may be applied to stent 10with a brush. Finally, in a preferred embodiment, the coating solutionmay be sprayed onto stent 10. Airbrushes suitable for spraying asolution of this type are commercially available from Badger Air-Brushof Franklin Park Ill.

Solvent selection is critical to a functioning surface treatment. It isessential that the solvent is capable of placing the polymer intosolution, and that the solvent and polymer chosen do not materiallyalter the therapeutic character of the therapeutic agent. On the otherhand, the therapeutic agent needs only to be dispersed throughout thesolvent. The therapeutic agent, therefore, may be either in a truesolution with the solvent or dispersed in fine particles within thesolvent.

Examples of some suitable polymer/solvent/therapeutic agent combinationscan include: polylactic acid/trichloroethane/colchicine;polyurethane/tetrahydrofuron/Taxol;(PLA/PCL,)/dimethylformamide/hirudin;(PLA/PGA)/ethylacetate/ticlopidine; and polyethyleneoxide/ethanol/heparin. It should be understood that these combinationsare merely exemplary, and it is recognized that other combinations arepossible.

FIG. 2 shows a magnified, partial plan view of stent 10, including wires12 and openings 16. The surfaces of stent 10 are covered with apolymeric coating 28. Polymeric coating 28 is created by applying asolution preferably including polymer, solvent, and therapeutic agent tothe surfaces of stent 10 then allowing the solvent to evaporate, therebyleaving on the stent surface a coating of the polymer and thetherapeutic agent. A number of processes may be used to apply thecoating solution to stent 10, including spraying, dipping, brushing,etc.

It is preferred that polymeric coating 28 be evenly distributed overstent 10. Although the procedures for applying the polymeric surfacetreatments are optimized, they still often leave polymeric fibers,polymeric particles, or other polymeric surface aberrations orimperfections on stent 10. These aberrations or imperfections inpolymeric coating 28 are illustrated in FIG. 2. Polymeric imperfections30 may take on numerous shapes and sizes. Regardless of the applicationprocess utilized, several types of imperfections 30 are common. Examplesof these imperfections 30 are polymeric fibers 32 which span theopenings 16 of the skeletal framework 15, and lumps 34 created by anoverabundance of polymeric material in one location. Imperfections 30 inpolymeric coating 28 may be the result of disproportionate applicationof the coating solution, or the settling of excessive material in aparticular location. At a minimum, imperfections 30 are unsightly. Moreimportantly, however, imperfections 30 may create adverse secondaryeffects.

The adverse secondary effects which may arise are correlated to the typeof polymeric imperfections 30. Polymeric fibers 32 are prone to twoadverse effects; fibers 32 may dislodge from stent 10 or they mayrelease their therapeutic agents into the blood stream. Becausepolymeric fibers 32 span across openings 16 of stent 10, they areattached typically at few locations. Expansion of stent 10 may dislodgethese imperfections 32, sending them within the circulatory system. Atthis point, there exists no control over the drug deliveringcapabilities of these rogue fibers 32. The release of drugs in undesiredlocations is likely to cause secondary effects. On the other hand,polymeric fibers 32 may remain attached to stent 10. Some of thepolymeric fibers 32 which remain attached to stent 10 may not engage thewall of the blood vessel. In this instance, the entire surface area ofthese polymeric fibers 32 is free to release therapeutic agent directlyinto the blood stream, causing other secondary effects.

Polymeric lumps 34 caused by an overabundance of polymeric material in alocalized area may also cause secondary effects. As mentioned above, thegoal of applying a polymeric surface treatment upon a stent 10 is tohave uniform coverage and uniform release of a therapeutic substance.When there are areas of excess coverage on stent 10, the targeteddiseased tissue may receive a non-uniform dosage of the releasedtherapeutic agent. For therapeutic agents, especially ones which promoteor restrict endothelial cell growth, uneven release may causenon-optimal treatment. Another problem created by lumps 34 is that thelumps 34 may be in a location on stent 10 where they do not contact thewall of the blood vessel. In this instance, the entire surface area ofthe lumps 34 will be free to release therapeutic agent directly into theblood stream, causing other secondary effects.

FIG. 3 is a plan view of a stent 10 and a tool 300. As describedpreviously, stent 10 includes wires 12, openings 16, and a lumen 20. Astream 302 of a gas 304 is shown exiting tool 300. In a preferredembodiment, tool 300 includes a generally tubular member 306 having alumen extending therethough which is open at a distal end 322. The outerdiameter of tubular member 306 is selected so that distal end 322 oftool 300 may readily enter lumen 20 of stent 10. A number of materialsmay be used to fabricate tool 300 including metallic and non-metallicmaterials. In a preferred embodiment, tool 300 is fabricated fromhypodermic tubing. Hypodermic tubing is preferred because it is readilyavailable with an appropriate outer diameter.

Tool 300 is in fluid communication with a supply (not shown) ofcompressed gas 304. Compressed gas 304 is preferably compressed airbecause it is inexpensive and readily available. Other gasses 304 may beused without departing from the spirit and scope of this invention. Forexample, acceptable results may be obtained using helium, nitrogen,argon, and carbon dioxide. Other gases may also be suitable for thisapplication, including gasses which are not normally present in air.Compressed gas 304 is released to atmosphere through tool 300 to createstream 302.

Tool 300 may be moved as indicated by a direction vector 310 in FIG. 3.When tool 300 is moved in the direction indicated by vector 310, tool300 is made to enter lumen 20 of stent 10. Tool 300 may also be rotatedas illustrated by direction vector 312, to change the angle at whichstream 302 strikes the surfaces of stent 10.

Tool 300 of FIG. 3 may be used in conjunction with a method of applyinga polymer coating 28 to stent 10. The process begins with the step ofpreparing a coating solution preferably including a polymer, a solvent,and a therapeutic substance. The coating solution is then applied to thestent by dipping, spraying, or any other acceptable method. Tool 300 isthen used to direct gas stream 302 so that it impinges on the surfacesof stent 10. When gas 304 of gas stream 302 strikes the surfaces ofstent 10 it displaces excess coating solution.

Tool 300 may be moved to direct gas stream 302 at stent 10 from aplurality of different locations and from a plurality of differentangles. For example, tool 300 may be moved as shown by vector 310 sothat tool 300 passes partially or completely through lumen 20 of stent10. Tool 300 may also be rotated as shown by vector 312 so that gasstream 302 strikes stent 10 at a plurality of angles. The position oftool 300 relative to stent 10 may also be changed without deviating fromthe spirit and scope of the invention.

The flow of gas 304 through openings 16 and around wires 12 issufficient to displace excess coating solution. Any lumps, fibers, etc.formed by the coating solution will be blown off the surfaces of stent10 or distributed more evenly over such surfaces by gas stream 302. Oncethe excess coating solution has been removed from or redistributed onthe surfaces of stent 10, the remaining solution on the stent which isstill liquid generally distributes evenly across the surface of thestent 10. The solvent in the coating solution is then allowed toevaporate thereby leaving on the surfaces of stent 10 a polymer coating28. As described above, polymer coating 28 ideally includes atherapeutic agent. Because all imperfections were removed before thecoating solution was allowed to dry, the polymer coating 28 resultingfrom this process is evenly distributed across the surfaces of stent 10.

FIG. 4 shows a magnified, partial plan view of stent 10, including wires12 and openings 16. A polymeric coating 28 has been applied to stent 10of FIG. 4 using the method described above. A coating solution includingpolymer, solvent, and therapeutic agent is applied to stent 10, excesscoating was removed from stent 10, and the remaining solution on thestent which is still generally liquid, distributes evenly across thesurface of the stent. The solvent was allowed to evaporate, therebyleaving on the stent surface a coating of the polymer and thetherapeutic agent. As seen in FIG. 4, the resulting polymer coating isevenly distributed across the surfaces of stent 10. As describedpreviously, polymeric coating 28 includes a polymer and a therapeuticagent, in a preferred embodiment. In an alternate embodiment, polymericcoating 28 may be comprised of a polymer.

FIG. 5 is a plan view of a stent 10 and an alternate tool 500. Asdescribed previously, stent 10 includes wires 12, openings 16, and alumen 20. A plurality of gas streams 502 are shown exiting tool 500. Ina preferred embodiment, tool 500 includes a tubular member 506 and anend cap 508. Tubular member 506 includes a lumen 520 and a plurality ofapertures 530. Apertures 530 provide a fluid passage from lumen 520 oftubular member 506 to the atmosphere surrounding tubular member 506.Although apertures 530 are illustrated as slots in FIG. 5, it should beunderstood that other embodiments of apertures 530 are possible withoutdeviating from the spirit and scope of the invention. For example,apertures 530 may be round holes.

Tool 500 is in fluid communication with a supply (not shown) ofcompressed gas 504. The compressed gas 504 is released to atmospherethrough tool 500 to create streams 502. Tool 500 may be moved asindicated by a direction vector 510 in FIG. 5. In this manner, tool 500may be moved through lumen 520 of stent 10, so that streams 502 may bepassed along the entire length of stent 10. Tool 500 may also be rotatedas illustrated by direction vector 512. Rotating tool 500 allows streams502 to pass across the entire circumference of stent 10.

Tool 500 of FIG. 5 may be used in conjunction with a method of applyinga polymer coating 28 to stent 10. The process begins with the step ofpreparing a coating solution preferably including a polymer, a solvent,and a therapeutic substance. The coating solution is then applied to thestent by dipping, spraying, or any other acceptable method. Tool 500 isthen used to direct gas streams 502 so that they impinge on the surfacesof stent 10. When gas 504 of gas streams 502 strikes the surfaces ofstent 10 it displaces excess coating solution.

During this process, tool 500 may be rotated and moved in a lineardirection. For example, tool 500 may be in continuous rotary motion asindicated by vector 512, such that streams 502 generally impinge on theentire circumference of stent 10. By way of a second example, tool 500may be moved in a linear direction, so that streams 502 pass across theentire length of stent 10. It should be understood that tool 500 may bemoved in a manner different than that shown in the above exampleswithout deviating from the spirit and scope of the invention.

The flow of gas 504 through openings 16 and around wires 12 issufficient to displace excess coating solution (e.g. any lumps, fibers,etc. formed by the coating solution will be blown off the surfaces ofstent 10 by gas streams 502). Once the excess coating solution has beenremoved from or redistributed on the surfaces of stent 10, the remainingliquid solution generally distributes evenly over the stent surface 10.The solvent in the coating solution is allowed to evaporate therebyleaving on the surfaces of stent 10 a polymer coating 28, whichpreferably includes a therapeutic agent. Because all imperfections wereremoved before the coating solution was allowed to dry, the polymercoating 28 resulting from this process is evenly distributed across thesurfaces of stent 10.

FIG. 6 is a plan view of a stent 10 and a tool 600. As describedpreviously, stent 10 includes wires 12, openings 16, and a lumen 20. Aplurality of gas streams 602 are shown exiting tool 600. In a preferredembodiment, tool 600 includes a tubular member 606 and an end cap 608.Tubular member 606 includes a lumen 620 and a plurality of apertures630. Apertures 630 provide a fluid passage from lumen 620 of tubularmember 606 to the atmosphere surrounding tubular member 606. In theembodiment of FIG. 6, apertures 630 are slots which are generallyperpendicular to the axis of tubular member 606. As seen in FIG. 6,apertures 630 extend beyond the center of tubular member 606.

Lumen 620 of tool 600 is in fluid communication with a supply (notshown) of compressed gas 604. Compressed gas 604 is released toatmosphere through apertures 630 in tool 600 to create streams 602. Asdescribed above, the embodiment of FIG. 6 includes apertures 630 whichare slots extending beyond the center of tubular member 606. As seen inFIG. 6, apertures 630 are adapted so that streams 602 of gas 604 mayexit tool 600 along its entire circumference. This arrangement ofapertures 630 creates a 360° pattern of streams 602 around tool 600.

Tool 600 may be moved as indicated by a direction vector 610 in FIG. 6.When tool 600 is moved in the direction indicated by vector 610, tool600 is made to travel through lumen 20 of stent 10.

Tool 600 of FIG. 6 may be used in conjunction with a method of applyinga polymer coating 28 to stent 10. The process begins with the step ofpreparing a coating solution preferably including a polymer, a solvent,and a therapeutic substance. The coating solution is then applied to thestent by dipping, spraying, or any other acceptable method. Tool 600 isthen used to direct gas streams 602 so that they impinge on the surfacesof stent 10. When gas 604 of gas streams 602 strikes the surfaces ofstent 10 it displaces excess coating solution. Tool 600 may be movedduring this process to assure that gas streams 602 impinge uponsubstantially all the surfaces of stent 10.

The flow of gas 604 through openings 16 and around wires 12 issufficient to displace excess coating solution (e.g. any lumps, fibers,etc. formed by the coating solution will be blown off the surfaces ofstent 10 by gas streams 602). Once the excess coating solution has beenremoved from the surfaces of stent 10, the remaining liquid solution onthe stent distributes evenly across the surface of the stent 10. Thesolvent in the coating solution is allowed to evaporate thereby leavingon the surfaces of stent 10 a polymer coating 28, which preferablyincludes a therapeutic agent. Because all imperfections were removedbefore the coating solution was allowed to dry, the polymer coating 28resulting from this process is evenly distributed across the surfaces ofstent 10.

FIG. 7 is a plan view of a stent 10, a tool 700, and a mandrel 730. Asdescribed previously, stent 10 includes wires 12, openings 16, and alumen 20. Tool 700 is similar to the tool of FIG. 3 being a generallytubular member having a lumen therethrough which is open at one end. Astream 702 of a gas 704 is shown exiting tool 700. In a preferredembodiment, tool 700 includes a tubular member 706 having a lumen 720and a distal end 708. Mandrel 730 is positioned so that its distal end732 is proximate distal end 708 of tubular member 706 creating a narrowfluid passage 734. The aperture size of tool 700 may be varied byaltering the position of the mandrel 730 relative to the distal end oftubular member 706. This will control the size and force of the gasstream impinging on the stent 10 with the gas jet being uniform over theentire circumference of the stent.

Tool 700 is in fluid communication with a supply (not shown) ofcompressed gas 704. The compressed gas 704 is released to atmospherethrough tubular member 706 and narrow fluid passage 734. When gas 704exits narrow fluid passage 734 it is traveling in a direction which willcause it to impinge on the surfaces of stent 10.

Tool 700 and mandrel 730 may be moved as indicated by a direction vector710 in FIG. 7. When tool 700 and mandrel 730 are moved in the directionindicated by vector 710, tool 700 and mandrel 730 may be made to passthrough lumen 20 of stent 10.

Tool 700 and mandrel 730 of FIG. 7 may be used in conjunction with amethod of applying a polymer coating 28 to stent 10. The process beginswith the step of preparing a coating solution preferably including apolymer, a solvent, and a therapeutic substance. The coating solution isthen applied to the stent by dipping, spraying, or any other acceptablemethod. Tool 700 and mandrel 730 are then used to direct gas stream 702so that it impinges on the surfaces of stent 10. When gas 704 of gasstream 702 strikes the surfaces of stent 10 excess coating solution isdisplaced. Tool 700 and mandrel 730 may be moved during this process toassure that gas stream 702 impinges upon substantially all the surfacesof stent 10.

The flow of gas 704 through openings 16 and around wires 12 issufficient to displace excess coating solution (e.g. any lumps, fibers,etc. formed by the coating solution will be blown off the surfaces ofstent 10 by gas stream 702). Once the excess coating solution has beenremoved from or redistributed on the surfaces of stent 10, remainingliquid solution generally distributes evenly across the surface of thestent 10. The solvent in the coating solution is allowed to evaporatethereby leaving on the surfaces of stent 10 a polymer coating 28, whichpreferably includes a therapeutic agent. Because all imperfections wereremoved before the coating solution was allowed to dry, the polymercoating 28 resulting from this process is evenly distributed across thesurfaces of stent 10.

It should be understood that the coating method described above may beused in conjunction with any stent design. For example, this coatingmethod may be used with both self-expanding and balloon expandablestents. The coating method described above may also be used withimplantable medical devices other than stents. For example, a thrombosisfilter may be coated using the coating method described above.

FIG. 8 is a perspective view of a thrombosis filter 820. Thrombosisfilter 820 includes a body member 822 and a plurality of elongatedstruts 824. Struts 824 each having a joined end 826 and a free end 828.Joined end 826 of each strut 824 is fixedly attached to body member 822.

Struts 824 may be comprised of any biocompatible material possessing thestructural and mechanical attributes necessary to retain thrombus filter820 in a blood vessel and capture thrombi. The material of struts 824may be a single material or a combination of materials. The material ofstruts 824 may be metallic or non-metallic. Stainless steel, titanium,tantalum, and nickel-titanium alloys have all been found to beacceptable metallic materials for struts 824. Preferred non-metallicmaterials may be selected from the following list, which is notexhaustive: poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA),polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA),poly(L-lactide-co-glycolide) (PLLA/IPGA), poly(D,L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co-trimethylenecarbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS),polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene),polyD,L-lactide-co-caprolactone) (PLA/PCL),poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN),poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxybutyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate),polyurethane, polysiloxane and their copolymers.

Struts 824 radiate outwardly from body member 822 such that thrombosisfilter 820 is generally conical in shape. When thrombosis filter 820 isdeployed inside a blood vessel, free ends 828 engage the blood vesselwall. Body member 822 is held in a position proximate the center of theblood vessel by the plurality of struts 824 which engage the bloodvessel walls with opposing force vectors.

The walls of the blood vessel are lined with a thin inner membrane,referred to as an intima or as a thelium. When thrombus filter 820 isimplanted in a blood vessel, the thelium is disrupted by free ends 828of struts 824. When free ends 828 of struts 824 disrupt this innermembrane, the body responds with a process which may be referred to asneointimal hyperplasia, or endothelial growth. As a result of thisprocess, the disrupted area of the thelium is overgrown with a number ofnew cells.

In a short time, free ends 828 of struts 824 become encapsulated withnew cell growth. Due to this endothelial growth, thrombosis filtersplaced in the blood vessel of a patient become affixed in the bloodvessel walls within two weeks after being implanted. Because free ends828 of struts 824 become fixed to the blood vessel walls in this way,removal of thrombus filter 820 using minimally invasive methods will bedifficult if not impossible after it has been in place for more than twoweeks.

Applying a coating including a therapeutic substance in a polymericcarrier to thrombosis filter 820 may prevent endothelial growth fromencapsulating free ends 828 of struts 824. If encapsulation of free ends828 of struts 824 is partially or completely prevented, the ability toremove percutaneously remove thrombus filter 820 will be greatlyenhanced. The coating including the therapeutic substance may be appliedselectively to free ends 828 of struts 824. Alternately, the coating maybe applied to substantially all the surfaces of thrombosis filter 820.

When thrombosis filter 820 is disposed in a blood vessel, the conicalformation of struts 824 acts to trap, or capture blood clots. Thegenerally conical shape of the formation of struts 824 serves to urgecaptured blood clots toward the center of the blood flow. The flow ofblood around the captured blood clots allows the body's natural lysingprocess to dissolve the clots. Applying a coating including atherapeutic substance in a polymeric carrier to the vascular filter mayassist the body in dissolving blood clots.

A tool 900 which may be used in conjunction with a method of coatingthrombosis filter 820 is also shown in FIG. 8. A plurality of gasstreams 902 are shown exiting tool 900. In a preferred embodiment, tool900 is a generally tubular member including a lumen 910 and a pluralityof apertures 912. Apertures 912 provide a fluid passage from lumen 910of tool 900 to the atmosphere surrounding tool 900. Although apertures912 are illustrated as round holes in FIG. 8, it should be understoodthat other embodiments of apertures 912 are possible without deviatingfrom the spirit and scope of the invention. For example, apertures 912may be slots. Lumen 910 of tool 900 is in fluid communication with asupply (not shown) of compressed gas 904. Compressed gas 904 is releasedto atmosphere through tool 900 to create streams 902.

As was previously mentioned, tool 900 of FIG. 8 may be used inconjunction with a method of applying a polymer coating to thrombosisfilter 820. The process begins with the step of preparing a coatingsolution preferably including a polymer, a solvent, and a therapeuticsubstance. The coating solution is then applied to thrombosis filter 820by dipping, spraying, or any other acceptable method. Tool 900 is thenused to direct gas streams 902 so that they impinge on the surfaces ofthrombosis filter 820. When gas 904 of gas streams 902 strikes thesurfaces of thrombosis filter 820, it displaces excess coating solution.

To assure that gas streams 902 impinge upon substantially all thesurfaces of thrombosis filter 820, tool 900 may be rotated and moved ina linear direction. Tool 900 may also be moved to a position other thanthe position shown in FIG. 8 without deviating from the spirit or scopeof this invention.

The flow of gas 904 around struts 824 and body member 822 is sufficientto displace excess coating solution. Once the excess coating solutionhas been removed from or redistributed on the surfaces of thrombosisfilter 820, the solvent in the coating solution is allowed to evaporatethereby leaving on the surface of thrombosis filter 820 a polymercoating, which preferably includes a therapeutic agent. Because allimperfections were removed before the coating solution was allowed todry, the polymer coating resulting from this process is evenlydistributed across the surfaces of thrombosis filter 820.

Numerous advantages of the invention covered by this document have beenset forth in the foregoing description. It will be understood, however,that this disclosure is, in many respects, only illustrative. Changesmay be made in details, particularly in matters of shape, size, andarrangement of parts without exceeding the scope of the invention. Theinvention's scope is, of course, defined in the language in which theappended claims are expressed.

What is claimed is:
 1. A method of applying a polymeric coating to amedical device, the method comprising the steps of:providing a medicaldevice having a plurality of surfaces; applying a polymeric material tothe plurality of surfaces of the medical device; and directing a streamof gas to impinge on the plurality of surfaces of the medicaldevice,wherein excess liquid polymeric material is removed from theplurality of surfaces of the medical device.
 2. The method of claim 1,wherein the stream of gas is directed by a generally tubular memberdefining a lumen and at least one aperture in fluid communication withthe lumen.
 3. The method of claim 2, wherein the at least one apertureis a hole.
 4. The method of claim 2, wherein the at least one apertureis a slot.
 5. The method of claim 1, wherein the polymeric materialincludes a solvent carrier.
 6. The method of claim 5, further includingthe step of evaporating at least a portion of the solvent carrier toform a dried coating.
 7. The method of claim 1, wherein the polymericmaterial is applied to the surface of the medical device by spraying. 8.The method of claim 1, wherein the polymeric material is applied to thesurface of the medical device by immersing the medical device in thepolymeric material.
 9. The method of claim 1, wherein the medical deviceis a stent.
 10. A method of applying a polymeric coating to a medicaldevice, the method comprising the steps of:providing a medical devicehaving a plurality of surfaces; providing a generally tubular memberdefining a lumen and at least one aperture in fluid communication withthe lumen; applying a polymeric material to the plurality of surfaces ofthe medical device; positioning the tubular member proximate the medicaldevice; and releasing a stream of gas through the generally tubularmember so that it impinges on the plurality of surfaces of the medicaldevice, wherein excess polymeric material is removed from the surface ofthe medical device.
 11. The method of claim 10, wherein the at least oneaperture is a hole.
 12. The method of claim 10, wherein the at least oneaperture is a slot.
 13. The method of claim 10, wherein the polymericmaterial includes a solvent carrier.
 14. The method of claim 13, furtherincluding the step of evaporating at least a portion of the solventcarrier to form a dried coating.
 15. The method of claim 10, wherein thepolymeric material is applied to the surface of the medical device byspraying.
 16. The method of claim 10, wherein the polymeric material isapplied to the surface of the medical device by immersing the medicaldevice in the polymeric material.
 17. The method of claim 10, whereinthe medical device is a stent.
 18. A method of applying a polymericcoating to a stent, the method comprising the steps of:providing a stenthaving a plurality of surfaces defined by a plurality of interconnectingstruts with open interstitial spaces therebetween; the stent including alumen extending through at least a portion thereof; providing agenerally tubular member defining a lumen and at least one aperture influid communication with the lumen; applying a polymeric material to theplurality of surfaces of the stent; positioning the tubular memberinside the lumen of the stent; releasing a compressed gas to atmospherethrough the tubular member; and wherein, gas exits the tubular memberthrough the at least one aperture and travels through the interstitialspaces of the stent.
 19. The method of claim 18, wherein the at leastone aperture is a hole.
 20. The method of claim 18, wherein the at leastone aperture is a slot.